Radiation imaging apparatus and radiation imaging system

ABSTRACT

A portable radiation imaging apparatus including: a detection section which includes a plurality of radiation detection elements for accumulating electric charges corresponding to a radiation amount, the radiation detection elements being two-dimensionally arranged; and a control section which controls accumulation of the electric charges in the radiation detection elements and reading of the accumulated electric charges from the radiation detection elements and generates a plurality of frame images of a subject, the electric charges to be accumulated corresponding to the radiation amount of radiation emitted in a pulsed manner by a radiation source and transmitted through the subject, wherein the control section adjusts a synchronization timing between the radiation source and the detection section by using a waveform of radiation emitted by the radiation source, the waveform being obtained by reading electric charges from at least a part of the plurality of radiation detection elements.

CROSS-REFERENCE TO RELATED APPLICATIONS

This application is a continuation of U.S. patent application Ser. No.15/346,924, filed on Nov. 9, 2016, which claimed the priority ofJapanese Application No. 2015-237102 filed on Dec. 4, 2015, the priorityof both applications is claimed and the entire content of bothapplications are hereby incorporated by reference.

BACKGROUND OF THE INVENTION 1. Field of the Invention

The present invention relates to a radiation imaging apparatus and aradiation imaging system.

2. Description of Related Art

In recent years, there have been known radiation imaging systems usingportable radiation imaging apparatuses (such as an FPD (Flat PanelDetector)) each of which includes two-dimensionally arranged radiationdetection elements for accumulating electric charges corresponding toradiation emitted from a radiation source and transmitted through asubject and reads out the electric charges accumulated in the radiationdetection elements to generate image data. Such radiation imagingsystems require synchronization between a radiation emission period foremitting radiation in the radiation source and an electric chargeaccumulation period for accumulating electric charges in the radiationimaging apparatus in order to perform the radiation emission by theradiation source during the electric charge accumulation period.

However, in a case where a radiation imaging apparatus wirelesslycommunicates with a radiation control apparatus which controls aradiation source, due to a problem in real time property, thesynchronization is possibly not achieved by performing synchronizedcommunication for each radiation emission between the radiation controlapparatus and the radiation imaging apparatus when performing dynamicimaging of emitting pulsed-radiation (pulse emission) at a predeterminedtime interval and obtaining a plurality of frame images.

Thus, for example, Patent document 1 (Patent Application Laid OpenPublication No. 2010-81960) describes a technique of providing a timemeasurement section to measure time in a console as a radiation controlapparatus which performs imaging instruction, further providing a timemeasurement section to measure time which is synchronized with the timemeasurement section of the console to an electronic cassette containingan FPD therein, controlling each of the time measurement sections tomeasure time, emitting radiation from a radiation source for apredetermined period of time from exposure start time which wasdetermined in advance in the console, and generating image dataindicating a radiation image by reading out electric charges accumulatedin the FPD after the predetermined period of time elapses from theexposure start time in the electronic cassette.

However, in many cases, the portable radiation imaging apparatus is usedin environment such as between a patient and a bed in which heat is keptand temperature easily rises. Thus, the heat release may not besufficiently ensured in the portable radiation imaging apparatus. On theother hand, the radiation control apparatus naturally releasessufficient heat with respect to the heat generation amount even duringoperation, and thus the influence of heat generation is negligible.Thus, even when the clocks are synchronized between the radiationcontrol apparatus and the radiation imaging apparatus in advance, theradiation emission period and electric charge accumulation period may beout of synchronization (synchronization deviation may be generated) insome cases due to the influence of change in oscillator operationfrequency caused by the temperature rise of the radiation imagingapparatus.

Also in a case where fluctuation is generated in the output of radiationemitted from the radiation source, the radiation emission period and theelectric charge accumulation period may be out of synchronization.

In a case where the synchronization deviation is generated at dynamicimaging to generate a plurality of frame images and radiation is emittedalso during a reading period after the electric charge accumulationperiod ends, for example, there remain electric charges corresponding tothe radiation emitted in the reading period, and thus deterioration inimage quality is generated in the next frame image.

SUMMARY OF THE INVENTION

An object of the present invention is to suppress deterioration of imagequality caused by the synchronization deviation between the radiationemission period in the radiation source and the electric chargeaccumulation period in the radiation imaging apparatus.

In order to solve the above problems, according to one aspect of thepresent invention, there is provided a portable radiation imagingapparatus including: a detection section which includes a plurality ofradiation detection elements for accumulating electric chargescorresponding to a radiation amount, the radiation detection elementsbeing two-dimensionally arranged; and a control section which controlsaccumulation of the electric charges in the radiation detection elementsand reading of the accumulated electric charges from the radiationdetection elements and generates a plurality of frame images of asubject, the electric charges to be accumulated corresponding to theradiation amount of radiation emitted in a pulsed manner by a radiationsource and transmitted through the subject, wherein the control sectionadjusts a synchronization timing between the radiation source and thedetection section by using a waveform of radiation emitted by theradiation source, the waveform being obtained by reading electriccharges from at least a part of the plurality of radiation detectionelements.

According to another aspect of the present invention, there is provideda radiation imaging system including: a radiation source which iscapable of pulse emission; and the above radiation imaging apparatus.

BRIEF DESCRIPTION OF THE DRAWINGS

The above and other objects, advantages and features of the presentinvention will become more fully understood from the detaileddescription given hereinafter and the appended drawings which are givenby way of illustration only, and thus are not intended as a definitionof the limits of the present invention, and wherein:

FIG. 1 is a view showing an entire configuration example of a radiationimaging system in an embodiment;

FIG. 2 is a block diagram showing a functional configuration of aradiation control apparatus;

FIG. 3 is a block diagram showing a functional configuration of an FPDcassette in first and second embodiments;

FIGS. 4A and 4B are views each showing examples of the operation of FPDcassette, read electric charge amount and radiation tube voltage when aline L0 (Line 0) is re-read after the end of reading electric charges inradiation detection elements for generating a frame image;

FIGS. 5A and 5B are views each showing examples of operation of FPDcassette, read electric charge amount and radiation tube voltage whenthe line L0 (Line 0) and line L1 (Line 1) are re-read after the end ofreading electric charges in radiation detection elements for generatinga frame image;

FIG. 6 is a block diagram showing a functional configuration of the FPDcassette in a third embodiment;

FIG. 7 is a block diagram showing information flow according tomeasurement and adjustment of time of the control section of FIG. 6; and

FIG. 8 is a flowchart showing clock adjustment processing executed bythe control section of FIG. 6.

DETAILED DESCRIPTION OF THE PREFERRED EMBODIMENT First Embodiment

(Configuration of Radiation Imaging System 100)

First, the configuration of a first embodiment according to the presentinvention will be described.

FIG. 1 shows an entire configuration example of a radiation imagingsystem 100 in the embodiment.

The radiation imaging system 100 is, for example, a system for doctor'srounds to perform radiation imaging to patients who cannot move easily,and configured by including a radiation control apparatus 1, a radiationsource 2 and an FPD (Flat Panel Detector) cassette 3. The radiationcontrol apparatus 1 has wheels and is configured as a mobile cart fordoctor's rounds which is capable of moving.

As shown in FIG. 1, the radiation imaging system 100 is a system whichis brought into an operating room, an intensive care unit, a hospitalroom Rc and such like, and performs dynamic imaging of a subject H byemitting radiation from the radiation source 2 while the FPD cassette 3is inserted, for example, between a bed B and the subject H lying on thebed B or into an insertion opening (not shown in the drawings) providedin the bed B on the opposite side to the subject H. In the embodiment,the dynamic imaging is obtaining a dynamic image by repeatedly emittingpulsed radiation such as X-ray (pulse emission) to the subject H at apredetermined time interval in response to one imaging operation(operation of exposure switch 102 a). A series of images obtained by thedynamic imaging is referred to as a dynamic image. Each image in theplurality of images forming the dynamic image is referred to as a frameimage.

Hereinafter, apparatuses forming the radiation imaging system 100 willbe described.

The radiation control apparatus 1 is an apparatus which controls theradiation source 2 to emit radiation on the basis of radiation emissionconditions which were input. As shown in FIG. 2, the radiation controlapparatus 1 is configured by including a control section 101, anoperation section 102, a display section 103, a storage section 104, adrive section 105, a wireless communication section 106, a crystaloscillator 107 and such like.

The control section 101 is configured by including a CPU (CentralProcessing Unit), a RAM (Random Access Memory) and such like. The CPU ofthe control section 101 reads out system programs and various types ofprocessing programs stored in the storage section 104 to load them intothe RAM according to the operation of the operation section 102 andcontrols the operations of the sections in the radiation controlapparatus 1 according to the loaded programs.

The operation section 102 has a touch panel or the like with transparentelectrodes disposed in a reticular pattern so as to cover the surface ofthe display section 103, detects the position pressed bya finger, atouch pen or the like, and outputs the positional information asoperation information to the control section 101.

The operation section 102 also includes the exposure switch 102 a for animaging operator to instruct exposure of radiation. The exposure switch102 a is a two-step switch.

The display section 103 is configured by including a monitor such as anLCD (Liquid Crystal Display) and a CRT (Cathode Ray Tube), and performsdisplay according to an instruction of display signal input from thecontrol section 101.

The storage section 104 is configured by including a non-volatilesemiconductor memory, a hard disk and such like. The storage section 104stores data such as various programs executed by the control section101, parameters necessary for executing processing of the programs andthe processing results.

The drive section 105 is a circuit for driving an X-ray tube or the likeof the radiation source 2. The drive section 105 is connected to theradiation source 2 via a cable.

The wireless communication section 106 includes an antenna 108, andperforms wireless communication with external equipment such as the FPDcassette 3.

The crystal oscillator 107 is an element which oscillates bypiezoelectric effect, and the oscillation number is input to the CPU ofthe control section 101. The control section 101 measures time on thebasis of the oscillation number input from the crystal oscillator 107.

The radiation source 2 is capable of pulse emission and emits radiation(X-ray) to the subject H in accordance with control of the radiationcontrol apparatus 1.

The FPD cassette 3 is a portable radiation imaging apparatus capable ofdynamic imaging. Hereinafter, the FPD cassette 3 is described as anindirect type apparatus which includes a scintillator and such like,converts the emitted radiation into light of other wavelengths such asvisible light with the scintillator and obtains image data from theradiation detection elements. However, the radiation imaging apparatusmay be a direct type apparatus which directly detects radiation with theradiation detection elements, not via the scintillator and such like.

FIG. 3 is a block diagram showing an equivalent circuit of the FPDcassette 3. As shown in FIG. 3, the FPD cassette 3 has a plurality ofradiation detection elements 7 which are two-dimensionally (matrixpattern) disposed on a sensor substrate not shown in the drawings(detection section). Each of the radiation detection elements 7accumulates electric charges corresponding to the amount of emittedradiation. The radiation detection elements 7 are connected torespective bias lines 9, and the bias lines 9 are connected to aconnection 10. The connection 10 is connected to a bias power supply 14,and reverse bias voltage is applied to the radiation detection elements7 via the respective bias lines 9 from the bias power supply 14.

The radiation detection elements 7 are connected to respective thin filmtransistors (hereinafter, referred to as TFTs) 8 as switch elements, andthe TFTs 8 are connected to signal lines 6. In a scanning drive section15, on voltage and off voltage supplied from a power circuit 15 a via awiring 15 c are switched in a gate driver 15 b and applied to lines L0to Lx of scanning lines 5. When the on voltage is applied via thescanning lines 5, the TFTs 8 are turned on and release the electriccharges accumulated in the radiation detection elements 7 to the signallines 6. When the off voltage is applied via the scanning lines 5, theTFTs 8 are turned off and interrupt the conduction between the radiationdetection elements 7 and the signal lines 6 to accumulate, in theradiation detection elements 7, the electric charges generated in theradiation detection elements 7. The radiation detection elements 7 andthe TFTs 8 connected thereto form pixels.

A plurality of reading circuits 17 is provided in a reading IC 16, andthe reading circuits 17 are connected to respective signal lines 6. Inreading processing of image data, when the electric charges are releasedfrom the radiation detection elements 7, the electric charges flow intothe reading circuits 17 via the signal lines 6, and voltage valuescorresponding to the amount of electric charges flowed into therespective reading circuits 17 are output by amplifier circuits 18.Correlated double sampling circuits (each described as “CDS” in FIG. 3)19 read out the voltage values output from the amplifier circuits 18 asimage data of analog values, and output the image data downstream. Theoutput image data is sequentially transmitted via an analog multiplexer21 to an A/D converter 20, sequentially converted into image data ofdigital values by the A/D convertor 20 and output to a storage section23 to be sequentially stored.

The control section 22 is configured by including a computer, an FPGA(Field Programmable Gate Array) or the like (not shown in the drawings)in which a CPU (Central Processing Unit), a ROM (Read Only Memory), aRAM (Random Access Memory), an input output interface and such like areconnected to a bus. The control section 22 may be formed of a dedicatedcontrol circuit. The control section 22 is connected to the storagesection 23 which is configured by including a SRAM (Static RAM), a SDRAM(Synchronous DRAM), a NAND type flash memory and such like. The controlsection 22 is also connected to a wireless communication section 30which performs wireless communication with external equipment such asthe radiation control apparatus 1 via an antenna 29. Since the radiationcontrol apparatus 1 communicates with the FPD cassette 3 wirelessly, itis not necessary to connect the radiation control apparatus 1 with theFPD cassette 3 by a cable or the like when performing imaging duringdoctor's rounds, which is very convenient.

The control section 22 is connected to a built-in power supply 24 or thelike which supplies necessary electric power to functional sections suchas the scanning drive section 15, reading circuits 17, storage section23 and bias power supply 14. The control section 22 controls operationsof the above-mentioned scanning drive section 15 and reading circuits 17to make the radiation detection elements 7 accumulate electric chargescorresponding to the radiation amount, release the accumulated electriccharges to the signal lines 6 and to read out the released electriccharges as image data by the reading circuits 17, for example.

The control section 22 is further connected to the crystal oscillator25. The crystal oscillator 25 is an element which oscillates bypiezoelectric effect, and the oscillation number is input to the CPU ofcontrol section 22. The control section 22 measures time on the basis ofthe oscillation number which is input from the crystal oscillator 25.

Though the FPD cassette 3 may be brought by an imaging operator such asa radiological technician, the FPD cassette 3 can be conveyed by beinginserted into a cassette pocket 11 provided in the radiation controlapparatus 1 as the mobile cart for doctor's rounds since the FPDcassette 3 is relatively heavy and is possibly broken or becomes out oforder when it falls.

(Operation of Radiation Imaging System 100)

Next, the imaging operation in the radiation imaging system 100 will bedescribed.

First, the imaging operator performs preparation for imaging. Forexample, the imaging operator inputs (sets) radiation emissionconditions via the operation section 102 in the radiation controlapparatus 1. The radiation emission conditions include a tube current, atube voltage, a frame rate (number of frame images captured per unittime (1 second)), a total imaging time for one imaging, a total numberof frame images to be captured for one imaging, type of additionalfilter and radiation emission time per frame image, for example. Theimaging operator also performs positioning of the subject H, radiationsource 2 and the FPD cassette 3.

When the preparation for imaging is completed, the imaging operatorpresses the first-step switch of exposure switch 102 a. When thefirst-step switch of exposure switch 102 a is pressed, the controlsection 101 of the radiation control apparatus 1 activates the radiationsource 2 and transmits an activation signal to the FPD cassette 3 viathe antenna 108 by the wireless communication section 106. When thewireless communication section 30 receives the activation signal, thecontrol section 22 of FPD cassette 3 sequentially applies the on voltagefrom the gate driver 15 b (see FIG. 3) of scanning drive section 15 tothe lines L1 to Lx of scanning lines 5, and performs reset processing ofthe radiation detection elements 7 of removing the electric chargesremaining in the radiation detection elements 7 by releasing theelectric charges to the signal lines 6, for example. When the resetprocessing is finished, the control section 22 applies the off voltagefrom the gate driver 15 b to the lines L1 to Lx of scanning lines 5, andshifts to an electric charge accumulation state. The control section 22transmits an interlock release signal to the radiation control apparatus1 by the wireless communication section 30.

When the second-step switch of exposure switch 102 a is pressed, thecontrol section 101 of the radiation control apparatus 1 determineswhether the interlock release signal from the FPD cassette 3 is receivedby the wireless communication section 106. If the control section 101does not determine that the interlock release signal is received, thecontrol section 101 stands by for reception of interlock release signal.When the interlock release signal is received, on the basis of the setradiation emission conditions, the control section 101 calculatesradiation emission time to emit radiation by the radiation source 2 andreading start time to start reading by the FPD cassette 3 for generatingframe images of dynamic imaging. The control section 101 transmits thereading start time to the FPD cassette 3 by the wireless communicationsection 106. The control section 101 controls the drive section 105 toperform radiation emission (pulse emission) on the radiation emissionconditions set in the radiation source 2 on the basis of the calculatedradiation emission time.

When the reading start time transmitted from the radiation controlapparatus 1 arrives, the control section 22 in the FPD cassette 3sequentially applies the on voltage from the gate driver 15 b to thelines L0 to Lx of the scanning lines 5 to perform reading processing ofimage data of frame images as mentioned above. When the readingprocessing of line Lx is finished, the control section 22 performsre-reading of electric charges in the radiation detection elements 7 fora single line, and determines whether or not an electric charge amountof the re-read electric line is a predetermined threshold or more. Thepredetermined threshold may be compared with a representative value (forexample, average value) of electric charge amounts of a plurality ofpixels of the re-read line, or the predetermined threshold may becompared with an electric charge amount of a single pixel.

FIG. 4A shows the operation of FPD cassette 3, read electric chargeamount and radiation tube voltage in a normal case (that is, when thereis no synchronization deviation between the radiation emission periodand the electric charge accumulation period) in the first embodiment.FIG. 4B shows the operation of FPD cassette 3, read electric chargeamount and radiation tube voltage when there is the synchronizationdeviation between the radiation emission period and the electric chargeaccumulation period (when the radiation emission period is delayed).Each of FIGS. 4A and 4B shows an example in which the electric chargesof radiation detection elements 7 on the line L0 (Line 0) are re-readafter the reading of electric charges of radiation detection elements 7of lines L0 to Lx is finished.

As shown in FIG. 4A, when there is no synchronization deviation betweenthe radiation emission period and the electric charge accumulationperiod, the electric charges in the radiation detection elements 7 ofthe re-read line L0 are nearly 0. However, as shown in FIG. 4B, when theend of radiation emission period is shifted afterwards to cross thereading period in a case where the time measured by the radiationcontrol apparatus 1 is delayed with respect to the time measured by theFPD cassette 3 or in a case where fluctuation is generated in theradiation output of radiation source 2, for example, the electriccharges corresponding to the radiation emitted in the reading period areaccumulated in the radiation detection elements 7. Thus, when theelectric charges in the radiation detection elements 7 of the line L0are re-read, the detected amount of electric charges is a predeterminedthreshold or more.

If it is not determined that the electric charge amount of the re-readline is the predetermined threshold or more, the control section 22determines that there is no synchronization deviation between theradiation emission period and the electric charge accumulation period,and continues the imaging sequence. If it is determined that theelectric charge amount of the re-read line is the predeterminedthreshold or more, the control section 22 determines that there issynchronization deviation between the radiation emission period and theelectric charge accumulation period, and continues the imaging sequenceafter adjusting the synchronization deviation on the basis of theelectric charge amount of the re-read line.

Though FIG. 4B shows, as an example, a case where the radiation emissionperiod is delayed with respect to the electric charge accumulationperiod, there is a case where the radiation emission period is advancedwith respect to the electric charge accumulation period. Also in thiscase, the electric charge amount of the re-read line (or pixel) is thepredetermined value or more. In many cases, the tendency of radiationemission period to be advanced or delayed with respect to the electriccharge accumulation period is known in advance according to thecharacteristics of crystal oscillators of radiation control apparatus 1and FPD cassette 3 and the radiation output characteristic of theradiation source 2.

Thus, in a case where it is known that the radiation emission periodtends to be delayed with respect to the electric charge accumulationperiod, for example, as shown in FIG. 4B, the control section 22 adjuststhe synchronization deviation between the radiation emission period andthe electric charge accumulation period by extending the electric chargeaccumulation period for generating the next frame image or providing awaiting time before the start timing of accumulation for the next frameimage. The reading start time for each of the frame images which havenot yet been captured is delayed for the amount of the extension ofaccumulation time or the waiting time with respect to the time notifiedfrom the radiation control apparatus 1.

In a case where it is known that the radiation emission period tends tobe advanced with respect to the electric charge accumulation period, thecontrol section 22 shortens the electric charge accumulation period forthe next frame image. The reading start time for each of the frameimages which have not yet been captured is advanced for the shortenedamount of the accumulation time with respect to the time notified fromthe radiation control apparatus 1.

The control section 22 repeatedly executes the above accumulation andreading processing to all the frame images, and generates a plurality offrame images forming the dynamic image of the subject H.

As described above, when the reading start time transmitted from theradiation control apparatus 1 arrives, the control section 22 of the FPDcassette 3 sequentially applies the on voltage from the gate driver 15 bto the lines L0 to Lx of the scanning lines 5 and performs readingprocessing of image data. When the reading processing of line Lx isfinished, the control section 22 performs re-reading of electric chargesin the radiation detection elements 7 for a single line and determineswhether there is synchronization deviation between the radiationemission period and the electric charge accumulation period on the basisof the electric charge amount of the re-read line. If there is thesynchronization deviation, the control section 22 adjusts thesynchronization deviation. Accordingly, it is possible to suppress thedeterioration of image quality due to the synchronization deviationbetween the radiation emission period and the electric chargeaccumulation period.

Second Embodiment

Next, a second embodiment will be described.

The configuration of radiation imaging system in the second embodimentis similar to that of radiation imaging system 100 described in thefirst embodiment, and thus the explanation thereof is omitted. Anoperation in the second embodiment will be described.

In the first embodiment, electric charges in the radiation detectionelements 7 are re-read for a single line each time the reading ofelectric charges in the radiation detection elements 7 for generating aframe image is finished. Then, the synchronization deviation between theradiation emission period and electric charge accumulation period isadjusted on the basis of electric charge amount in the radiationdetection elements 7 of the re-read single line. In the secondembodiment, the re-reading of electric charge amount in the radiationdetection elements 7 is performed for a plurality of lines each time thereading of electric charges from the radiation detection elements 7 forgenerating a frame image is finished. Then, the synchronizationdeviation is adjusted on the basis of electric charge amount in theradiation detection elements 7 for the re-read plurality of lines. Theoperation of radiation imaging system 100 is similar to that of thefirst embodiment until the arrival of reading start time in the FPDcassette 3, the reading start time being transmitted from the radiationcontrol apparatus 1. Thus, the explanation thereof is omitted.

When the reading start time transmitted from the radiation controlapparatus 1 arrives in the FPD cassette 3, the control section 22sequentially applies on voltage to the lines L0 to Lx of scanning lines5 from the gate driver 15 b and performs reading processing of imagedata for a frame image as described above. When the reading processingof line Lx is finished, the control section 22 re-reads electric chargesfrom the radiation detection elements 7 of a plurality of lines, anddetermines whether the electric charge amount in each of the re-readlines is a predetermined threshold or more. The predetermined thresholdmay be compared with a representative value (for example, average value)of electric charge amounts in a plurality of pixels of the re-read line,or the predetermined threshold may be compared with an electric chargeamount of a single pixel.

FIG. 5A shows the operation of FPD cassette 3, read electric chargeamount and radiation tube voltage in a normal case (that is, when thereis no synchronization deviation between the radiation emission periodand electric charge accumulation period) in the second embodiment. FIG.5B shows the operation of FPD cassette 3, read electric charge amountand radiation tube voltage when there is synchronization deviationbetween the radiation emission period and electric charge accumulationperiod (when the radiation emission period is advanced with respect tothe electric charge accumulation period) in the second embodiment. Eachof FIGS. 5A and 5B illustrates an example in which re-reading ofelectric charges is performed for the radiation detection elements 7 oflines L0 to L1 (Line 0 and Line 1) after the reading of lines L0 to Lxis finished.

As shown in FIG. 5A, when there is no synchronization deviation betweenthe radiation emission period and the electric charge accumulationperiod, the electric charge amounts in the radiation detection elements7 of the re-read lines L0 and L1 are nearly 0. However, as shown in FIG.5B, in a case where the start of radiation emission period is shifted tobe earlier such as a case where the time measured in the radiationcontrol apparatus 1 is advanced with respect to the time measured in theFPD cassette 3 and a case where fluctuation is generated in theradiation output of radiation source 2, the electric charges are alreadystored in the radiation detection elements 7 at the start time ofelectric charge accumulation period for generating the next frame image.In addition, as shown in FIG. 4B, in a case where the radiation emissionperiod is shifted afterwards with respect to the electric chargeaccumulation period and crosses the reading period, the electric chargescorresponding to the radiation emitted in the reading period areaccumulated in the radiation detection elements 7. Thus, the amount ofdetected electric charges is a predetermined threshold or more when theelectric charges are re-read from the radiation detection elements 7 ofthe plurality of lines such as the lines L0 and L1.

If it is not determined that the electric charge amount of the re-readplurality of lines is the predetermined threshold or more, the controlsection 22 determines that there is no synchronization deviation betweenthe radiation emission period and the electric charge accumulationperiod, and continues the imaging sequence.

If it is determined that the electric charge amount of the re-readplurality of lines is the predetermined threshold or more, the controlsection 22 determines whether the radiation emission period is delayedor advanced with respect to the electric charge accumulation period onthe basis of the electric charge amounts of re-read plurality of lines.On the basis of the determination result, the control section 22 adjustssynchronization between the radiation emission period and electriccharge accumulation period and continues the imaging sequence after theadjustment.

Specifically, among the electric charge amounts of the re-read pluralityof lines, if the electric charge amount of one re-read line is largerthan the electric charge amount of a re-read line which was re-readearlier than the one re-read line (for example, in a case shown in FIG.5B), the control section 22 determines that the radiation emissionperiod is advanced with respect to the electric charge accumulationperiod, and adjusts the synchronization deviation between the radiationemission period and electric charge accumulation period by shorteningthe electric charge accumulation period for generating the next frameimage. The reading start time for each of the frame images which havenot yet been captured is advanced for the shortened amount of theaccumulation time with respect to the time notified from the radiationcontrol apparatus 1.

Among the electric charge amounts of the re-read plurality of lines, ifthe electric charge amount of one re-read line is smaller than theelectric charge amount of a re-read line which was re-read earlier thanthe one re-read line, the control section 22 determines that theradiation emission period is delayed with respect to the electric chargeaccumulation period, and adjusts the synchronization deviation betweenthe radiation emission period and electric charge accumulation period byextending the electric charge accumulation period for generating thenext frame image or by providing a waiting time before the accumulationstart timing for generating the next frame image. The reading start timefor each of the frame images which have not yet been captured is delayedfor the amount of extension of electric charge accumulation period orthe amount of waiting time with respect to the time notified from theradiation control apparatus 1.

The control section 22 repeatedly executes the accumulation and readingprocessing for all the frame images and generates the plurality of frameimages forming the dynamic image of subject H.

In such way, when the reading start time transmitted from the radiationcontrol apparatus 1 arrives, the control section 22 of FPD cassette 3sequentially applies on voltage to lines L0 to Lx of scanning lines 5from the gate driver 15 b and performs reading processing of image dataof a frame image. When the reading processing of line Lx is finished,the control section 22 preforms re-reading of the radiation detectionelements 7 of a plurality of lines and determines whether there issynchronization deviation between the radiation emission period andelectric charge accumulation period on the basis of the electric chargeamounts of the plurality of re-read lines. If it is determined thatthere is synchronization deviation, the control section 22 determineswhether the electric charge accumulation period is delayed or advancedwith respect to the radiation emission period on the basis of theelectric charge amounts of the plurality of re-read lines, and adjuststhe synchronization deviation on the basis of the determination result.

Accordingly, in the second embodiment, the synchronization deviation canbe adjusted by determining whether the electric charge accumulationperiod is delayed or advanced with respect to the radiation emissionperiod for each frame. Thus, it is possible to suppress thedeterioration of image quality due to the synchronization deviationbetween the radiation emission period and the electric chargeaccumulation period even when the direction of synchronization deviationis not constant.

Third Embodiment

Next, the third embodiment of the present invention will be described.

FIG. 6 is a block diagram showing an equivalent circuit of FPD cassette3A in the third embodiment. As shown in FIG. 6, the FPD cassette 3A inthe third embodiment includes, in addition to the configuration of FPDcassette 3 described in the first embodiment, a temperature sensor 31which detects the temperature inside the housing of FPD cassette 3A andan A/D convertor 32 which converts a voltage output from the temperaturesensor 31 into a digital voltage value and outputs the converted valueto the control section 22.

The storage section 23 stores a clock adjustment table 231.

The frequency characteristic of vibration of crystal oscillator 25 withrespect to temperature is represented by a quadratic curve protrudingupward with an apex at 25° C., and the frequency is lower as thetemperature difference from 25° C. is larger. The clock adjustment table231 is a table in which a reference temperature is set to be 25° C.having the maximum operation frequency of crystal oscillator 25, andeach temperature difference from the reference temperature is associatedwith the oscillation number of crystal oscillator 25 corresponding to 1unit time (for example, 1 second) for the temperature difference on thebasis of the frequency characteristic of crystal oscillator 25.

The other configuration of FPD cassette 3A is similar to that of FPDcassette 3 described in the first embodiment, and thus, the explanationthereof is omitted.

Next, the operation in the third embodiment will be described.

FIG. 7 is a block diagram showing the information flow of measurementand adjustment of time in the control section 22.

As shown in FIG. 7, the oscillation number of crystal oscillator 25 isinput to a timer 222 in the CPU 221 of the control section 22. Theoscillation number (count setting value 222 a) corresponding to 1 unittime (for example, 1 second) is set in a register in the timer 222, andthe timer 222 outputs the clock to a CPU core 223 each time the setoscillation number is counted. The CPU core 223 measures time on thebasis of the clock from the timer 222. At the time of introduction intothe facility, the clock is corrected at a predetermined temperature(that is, 25° C.) at which the crystal oscillator 25 has a maximumoperation frequency. The same applies to the measurement and correctionof time in the radiation control apparatus 1.

However, in many cases, the FPD cassette 3A is used in an environment inwhich heat is kept and the temperature easily rises such as between asheet and a patient lying on a bed, and thus, the heat release possiblycannot be ensured sufficiently. On the other hand, the radiation controlapparatus 1 naturally releases sufficient heat with respect to the heatgeneration amount thereof even during operation, and thus the influenceof heat generation is negligible. Thus, even when the times aresynchronized between the radiation control apparatus 1 and the FPDcassette 3A in advance, the times are shifted from each other in somecases due to the influence of change in operation frequency of crystaloscillator 25 caused by temperature rise of the FPD cassette 3A.

In the third embodiment, the control section 22 executes clockadjustment processing (see FIG. 8) immediately before imaging. Forexample, when the pressing of first-step switch of the exposure switch102 a is detected in the radiation control apparatus 1 and theactivation signal is transmitted to the FPD cassette 3A via the antenna108 (when the activation signal is received by the wirelesscommunication section 30), the control section 22 of the FPD cassette 3Aperforms reset processing and executes clock adjustment processing shownin FIG. 8.

In the clock adjustment processing, the control section 22 first obtainsa temperature value from the temperature sensor 31, and determineswhether the obtained temperature is equal to a reference temperature(here, 25° C. which is the predetermined temperature having the maximumoperation frequency) (step S1).

If it is determined that the temperature obtained from the temperaturesensor 31 is equal to the reference temperature (step S1; YES), thecontrol section 22 executes imaging (step S3).

If it is not determined that the temperature obtained from thetemperature sensor 31 is equal to the reference temperature (step S1;NO), the control section 22 adjusts the timer 222 by reading out theoscillation number corresponding to the temperature difference betweenthe obtained temperature and the reference temperature from the clockadjustment table 231, and updating the count setting value 222 a of thetimer 222 with the read value (step S2). After the adjustment, thecontrol section 22 executes imaging (step S3).

In step S3, the control section 22 stands by for the end of resetprocessing. When the reset processing is finished, the control section22 shifts the state to the electric charge accumulation state byapplying the off voltage to the lines L1 to Lx of scanning lines 5 fromthe gate driver 15 b. The wireless communication section 30 transmitsthe interlock release signal to the radiation control apparatus 1. Whenthe reading start time by the FPD cassette 3A is received from theradiation control apparatus 1 and the reading start time arrives, thecontrol section 22 sequentially applies the on voltage to the lines L0to Lx of the scanning lines 5 from the gate driver 15 b and performsreading processing of image data as mentioned above. When the reading ofline Lx is finished, the control section 22 shifts to the accumulationstate for generating the next frame image, and accumulates the electriccharges corresponding to the radiation emitted from the radiation source2. When the reading start time arrives, the control section 22sequentially applies the on voltage to the lines L0 to Lx of scanninglines 5 from the gate driver 15 b and performs image data readingprocessing as mentioned above. The control section 22 repeatedlyexecutes accumulation and reading processing for all the frame imagesand generates the radiation image of the subject.

As described above, the control section 22 of the FPD cassette 3Aobtains the temperature from the temperature sensor 31 immediatelybefore the start of imaging, and if the obtained temperature is notequal to the reference temperature, the control section 22 performsclock adjustment of the timer 222 and shifts to imaging after theadjustment. Accordingly, it is possible to suppress the deterioration ofimage quality due to the synchronization deviation between the radiationemission period and the electric charge accumulation period caused bythe clock shift due to the influence of temperature.

As described above, the control section 22 of FPD cassette 3 in theradiation imaging system 100 adjusts the synchronization timing ofradiation source 3 and FPD cassette 3 by using the waveform of radiationemitted from the radiation source 3, the waveform being obtained byreading out the electric charges from at least a part of the pluralityof radiation detection elements 7. For example, the control section 22re-reads the electric charges from a part of the plurality of radiationdetection elements 7 after reading out electric charges from theplurality of radiation detection elements 7 for generating one frameimage of the dynamic image, and determines whether radiation was emittedduring a period other than the electric charge accumulation period ofradiation detection elements 7 on the basis of the electric chargeamount of the re-read radiation detection elements 7. If it isdetermined that the radiation was emitted during a period other than theelectric charge accumulation period of radiation detection elements 7,the control section 22 adjusts the electric charge accumulation periodso as to emit radiation within the electric charge accumulation periodwhen the next frame image is generated. Accordingly, it is possible tosuppress the deterioration of image quality due to the synchronizationdeviation between the radiation emission period in the radiation source2 and the electric charge accumulation period in the FPD cassette 3.

For example, the control section 22 of FPD cassette 3 re-reads electriccharges from the radiation detection elements 7 of a plurality of lines.If an electric charge amount of a re-read line is a predetermined valueor more and an electric charge amount of one re-read line is larger thanan electric charge amount of a re-read line which was re-read earlierthan the one re-read line, the control section 22 determines that theradiation emission period is advanced with respect to the electriccharge accumulation period, and shortens the electric chargeaccumulation period for generating the next frame image. Accordingly, ina case where the radiation emission period is advanced with respect tothe electric charge accumulation period, it is possible to detect theadvance and adjust so that radiation is emitted within the electriccharge accumulation period when the next frame image is generated.

If the electric charge amount of the re-read line is a predeterminedvalue or more and the electric charge amount of the one re-read line issmaller than the electric charge amount of the re-read line which wasre-read earlier than the one re-read line, the control section 22 of theFPD cassette 3 determines that the radiation emission period is delayedwith respect to the electric charge accumulation period, and extends theelectric charge accumulation period for generating the next frame imageor provides a waiting time before start of the electric chargeaccumulation period. Accordingly, in a case where the radiation emissionperiod is delayed with respect to the electric charge accumulationperiod, it is possible to detect the delay and adjust so that radiationis emitted within the electric charge accumulation period when the nextframe image is generated.

The descriptions of the embodiments are preferred examples of thepresent invention, and the present invention is not limited to theexamples. The detailed configurations and detailed operations of theapparatuses forming the radiation imaging system can be appropriatelymodified within the scope of the present invention.

What is claimed is:
 1. A portable radiation imaging apparatuscomprising: a detection section which includes a plurality of radiationdetection elements for accumulating electric charges corresponding to aradiation amount, the radiation detection elements beingtwo-dimensionally arranged; and a control section which controls, by asynchronization timing between a radiation source and the detectionsection that is determined in advance, accumulation of the electriccharges in the radiation detection elements and reading of theaccumulated electric charges from the radiation detection elements usingreading circuits, and generates a plurality of frame images of asubject, the electric charges to be accumulated corresponding to theradiation amount of x-ray radiation emitted in a pulsed manner by theradiation source and transmitted through the subject, wherein thecontrol section adjusts a deviation of the synchronization timingbetween the radiation source and the detection section based on theradiation amount.
 2. The radiation imaging apparatus according to claim1, wherein, after the reading of the electric charges from the pluralityof radiation detection elements for generating a frame image of theplurality of frame images, the control section re-reads electric chargesfrom a part of the plurality of radiation detection elements, anddetermines whether radiation is emitted during a period other than anelectric charge accumulation period of the radiation detection elementson the basis of the radiation amount of a re-read radiation detectionelement, and when the control section determines that radiation isemitted before or after the electric charge accumulation period of theradiation detection elements, the control section adjusts the electriccharge accumulation period so that radiation is emitted within theelectric charge accumulation period when a next frame image isgenerated.
 3. The radiation imaging apparatus according to claim 2,wherein, when the radiation amount of the re-read radiation detectionelement is a predetermined value or more, the control section determinesthat radiation is emitted before or after the electric chargeaccumulation period of the radiation detection elements.
 4. Theradiation imaging apparatus according to claim 2, wherein, the controlsection re-reads electric charges from radiation detection elements of aplurality of lines, and when the radiation amount of a re-read line is apredetermined value or more and the radiation amount of one re-read lineis larger than an electric charge amount of a line which is re-readearlier than the one re-read line, the control section determines thatthe radiation emission period is advanced with respect to the electriccharge accumulation period, and shortens the electric chargeaccumulation period when the next frame image is generated.
 5. Theradiation imaging apparatus according to claim 2, wherein, the controlsection re-reads electric charges from radiation detection elements of aplurality of lines, and when the radiation amount of a re-read line is apredetermined value or more and the radiation amount of one re-read lineis smaller than an electric charge amount of a line which is re-readearlier than the one re-read line, the control section determines thatthe radiation emission period is delayed with respect to the electriccharge accumulation period, and extends the electric charge accumulationperiod or provides a waiting time before start of the electric chargeaccumulation period when the next frame image is generated.
 6. Aradiation imaging system comprising: a radiation source which is capableof pulse emission; and the radiation imaging apparatus according toclaim
 1. 7. The radiation imaging apparatus according to claim 1,wherein the control section reads electric charges based on theradiation amount from the radiation detection elements of a plurality oflines, and adjusts the deviation of the synchronization timing betweenthe radiation source and the detection section based on the radiationamount.
 8. The radiation imaging apparatus according to claim 1,wherein, the control section adjusts the deviation of thesynchronization timing between the radiation source and the detectionsection based on an inclination of the radiation amount.
 9. Theradiation imaging apparatus according to claim 8, wherein, the controlsection adjusts the deviation of the synchronization timing between theradiation source and the detection section based on a difference of theelectric charge amount of two read lines.